High-power LED lamp body, meridian treatment instrument and skin optical phantom construction method

Abstract

The application discloses a high-power LED lamp body, a meridian treatment instrument and a skin optical phantom construction method in the fields of medical devices and optical detection technology, and relates to the technical field of medical devices and optical detection technology.The high-power LED lamp body comprises a gold-filled PCB board, and the gold-filled PCB board is used for providing a circuit conduction path.The application forms a porous silver solder paste layer by adopting a nano-silver paste sintering solidification technology, directly solidifies small crystal wafers of vertical structure LED on the gold-filled PCB substrate, forms a high-heat-conducting area by the porous silver solder paste layer, makes the porous silver solder paste layer cooperate with the gold-filled PCB board to rapidly dissipate heat, improves the overall heat dissipation performance of the high-power LED lamp body, increases the operation time length of the high-power LED lamp body, prolongs the service life, and the plurality of small crystal wafers of vertical structure LED are arranged in a preset arrangement mode to form a multi-wavelength LED light array.The multi-wavelength LED light array can provide LED light sources of preset wavelengths, and can meet the treatment requirements of different wavelengths of light for meridian treatment.

Description

Technical Field

[0001] This invention relates to the field of medical devices and optical detection technology, specifically a high-power LED lamp body, a meridian therapy instrument, and a method for constructing a skin optical phantom. Background Technology

[0002] Photobiological therapy uses low-energy lasers or light-emitting diode (LED) light sources to irradiate human tissues, producing photochemical effects rather than thermal effects, thereby promoting cell repair, reducing inflammation, and relieving pain. In recent years, LED light sources have been increasingly used in the development of meridian therapy devices due to their advantages such as low cost, long lifespan, and flexible wavelength selection.

[0003] However, existing LED meridian therapy devices have the following technical problems in application: (1) The heat dissipation performance of high-power LED lamps is insufficient, resulting in severe light decay and poor long-term operational stability; (2) The divergence angle of the light beam emitted by the LED is large, and the energy is dispersed after irradiating the skin surface, making it difficult to form an effective light dose in deep tissues, and the uniformity of irradiance in the central area is poor; (3) During the development of the therapy device, there is a lack of a phantom that can truly simulate the optical properties of human skin, resulting in inaccurate verification of the light dose penetration effect and affecting the optimization of treatment parameters. Summary of the Invention

[0004] The purpose of this invention is to provide a high-power LED lamp body, a meridian therapy instrument, and a method for constructing a skin optical phantom, in order to solve the problems mentioned above, such as poor heat dissipation performance, insufficient light penetration dose, poor center uniformity, and lack of reliable optical phantom verification methods for LED meridian therapy instruments.

[0005] To achieve the above objectives, the present invention provides the following technical solution: In a first aspect, the present invention provides a high-power LED lamp body, comprising: Immersion gold PCB board, wherein the immersion gold PCB board is used to provide circuit conduction path; A vertical structure LED chip, wherein the first connection end of the vertical structure LED chip is fixed to the first circuit conduction path of the immersion gold PCB board by nano silver paste sintering and die bonding technology, the nano silver paste forms a porous silver powder solder paste layer after sintering, the second connection end of the LED chip is connected to gold wire, and the other end of the gold wire is connected to the second circuit conduction path of the immersion gold PCB board. A plurality of the vertical structure LED chips are arranged in a preset arrangement to form a multi-wavelength LED light array, the multi-wavelength LED light array is used to provide a high-power LED light source of a preset wavelength; A protective component is connected to an immersion gold PCB board and covers the vertical structure LED chip and gold wire.

[0006] As a further aspect of the present invention: the protective component includes a frame fixed by UV-curing adhesive and a glass protective cover mounted on the frame. The frame is connected to an immersion gold PCB board. The frame and the glass protective cover are used to seal and protect the internal vertical structure LED chips and gold wires.

[0007] As a further aspect of the present invention, the preset wavelengths are 630nm, 830nm, and 940nm.

[0008] As a further aspect of the present invention, it also includes a composite material heat sink that is thermally coupled to the immersion gold PCB board. The composite material heat sink is combined with active thermal control technology to control the total thermal resistance of the lamp body within a preset range.

[0009] Secondly, the present invention provides an LED light source meridian therapy device, comprising a housing: A plurality of high-power LED lamp bodies are installed inside a housing, and the plurality of high-power LED lamp bodies are used to provide a high-power LED light source; An optical system is installed inside a housing. The optical system includes an optical integrating rod, one end of which is equipped with a high-power LED lamp body, and the other end of which is sequentially equipped with an aspherical condenser lens and a Fresnel lens. A multi-channel controller is mounted on the housing and is connected to each high-power LED lamp body. The multi-channel controller is used to collect and adjust the output parameters of several high-power LED lamp bodies in real time.

[0010] As a further aspect of the present invention: the aspherical condenser lens and Fresnel lens in the optical system control the divergence angle of the light source within 30° to form a stable light dose penetration in biological tissue.

[0011] As a further aspect of the present invention, the wavelength of the LED light source is selected from at least one of 630nm, 810nm or 940nm.

[0012] Thirdly, the present invention provides a method for constructing a skin optical phantom, the method comprising the following steps: S1: Establish a multi-layer skin optical model, which includes at least the epidermis, the dermis containing the upper vascular plexus and the deep vascular plexus, and the subcutaneous fat layer, and configure preset thickness, absorption coefficient and reduced scattering coefficient for each layer. S2: Using agar as a matrix, equipped with absorbents and scattering agents, and based on the optical parameters of the epidermis, dermis and subcutaneous fat layer, respectively, an epidermal phantom and a dermal phantom are cast and solidified to form an epidermal phantom and a dermal phantom. S3: Use an integrating sphere system to measure the diffuse reflectance and transmittance of the epidermal and dermal phantoms, and calculate the actual absorption coefficient and reduced scattering coefficient of each phantom layer based on the inverse Monte Carlo algorithm to ensure that they match the skin optical model. S4: The epidermal phantom and the dermal phantom are stacked in anatomical order, and physiological saline is added between the layers to form a multi-layered composite skin optical phantom.

[0013] As a further aspect of the present invention: the absorbent is prepared with Indian ink or whole pig blood, and the scattering agent is prepared with a fat emulsion; The formulation volume fraction of the epidermal phantom is: 1.5% agar, 0.005% Indian ink and 2% fat emulsion, and the thickness of the epidermal phantom is 1 mm; The dermal phantom comprises an upper dermal phantom and a deep dermal phantom. The upper dermal phantom has a volume fraction of 1.5% agar, 2% fat emulsion, and 1.5% whole pig blood. The deep dermal phantom has a volume fraction of 1.5% agar, 2% fat emulsion, and 1% whole pig blood. The thickness of both the upper and deep dermal phantoms is 2 mm.

[0014] As a further aspect of the present invention: the verification of the multilayer skin optical model and the skin optical phantom was completed through a correlation analysis of transmittance between Monte Carlo simulation and phantom experiments, and the calculated coefficient of determination R... 2 The value is not less than 0.9.

[0015] Compared with the prior art, the beneficial effects of the present invention are: 1. This invention utilizes nano-silver paste sintering and die-bonding technology to form a porous silver solder paste layer, directly bonding vertically structured LED chips onto an immersion gold PCB substrate. The porous silver solder paste layer forms a high thermal conductivity area, allowing it to work in conjunction with the immersion gold PCB board for rapid heat dissipation. This improves the overall heat dissipation performance of the high-power LED lamp body, avoids localized heat accumulation, increases the operating time of the high-power LED lamp body, and extends its lifespan. Furthermore, several vertically structured LED chips are arranged in a preset configuration to form a multi-wavelength LED light array. This multi-wavelength LED light array can provide LED light sources of preset wavelengths, meeting the therapeutic needs of meridian therapy for different wavelengths of light and improving therapeutic adaptability.

[0016] 2. This invention uses a housing to install the optical system and multi-channel controller. An aspherical condenser lens and a Fresnel lens are sequentially arranged at the other end of the optical integrating rod. The optical integrating rod fully mixes and homogenizes the light emitted from the light source, ultimately outputting a light spot that meets the requirements of acupoint irradiation, has the required uniformity, and is of the correct size. The multi-channel controller can independently control the working state of each high-power LED lamp, flexibly adjusting the output power of a single lamp or multiple lamps and emitting light sources of preset wavelengths according to actual treatment needs. This ensures the specificity and effectiveness of photobiological regulation, guarantees the stability and safety of the treatment process, and the device has a compact overall structure, making it easy to move and operate, and adaptable to the needs of different diagnostic and treatment scenarios.

[0017] 3. The skin optical phantom construction method proposed in this invention establishes a multi-layer optical model comprising at least the epidermis, a dermis containing vascular plexuses, and subcutaneous fat. Each layer of the phantom is then cast and solidified using specific formulations of agar-India ink-fat emulsion or agar-whole pig blood-fat emulsion. The absorption coefficient and reduced scattering coefficient of each layer are then calibrated using an integrating sphere system and an inverse Monte Carlo algorithm. Finally, the layers are superimposed to form a multi-layer composite skin optical phantom. The phantom prepared by this method highly matches the optical parameters of real skin. Furthermore, the optical equivalence of the phantom is ensured through correlation verification between Monte Carlo simulation and phantom experiments of transmittance. This method also provides a standardized and repeatable physical platform for testing the light penetration dose of LED light source meridian therapy devices. This allows for accurate evaluation of tissue penetration depth and energy deposition distribution at different divergence angles and wavelengths during the research and development stage of the therapy device, thereby optimizing treatment parameters and avoiding the risks and ethical issues associated with direct human trials. Attached Figure Description

[0018] Figure 1 This is a schematic diagram of the high-power LED lamp body packaging structure of the present invention; Figure 2 This is a schematic diagram of the LED module packaging provided by the present invention; wherein, Figure 2 (a) is a model and actual image of a high-power LED lamp body; Figure 2 (b) is the relative spectrum of the LED; Figure 2 (c) shows the LED light distribution curve and three-dimensional light distribution diagram; Figure 3 This is a schematic diagram of the overall structure of the LED light source meridian therapy device of the present invention; Figure 4 This is a schematic diagram of the optical path of the optical system of the present invention; Figure 5 This is a schematic diagram of the optical path simulation provided by the present invention; wherein, Figure 5 (a) is a simulation diagram of the overall optical path; Figure 5 (b) is a normalized illuminance distribution diagram of the light spot; Figure 5(c) is the light distribution intensity map at the line position in the illuminance diagram; Figure 6 This is a schematic diagram of the experimental optical path provided by the present invention; Figure 7 This is a schematic diagram of the method flow provided by the present invention; Figure 8 This is a schematic diagram of the skin structure provided by the present invention; Figure 9 This is a schematic diagram of the optical parameters of the skin optical model provided by the present invention; wherein, Figure 9 (a) represents the optical parameters of the epidermis; Figure 9 (b) represents the optical parameters of the dermis; Figure 9 (c) Optical parameters of the subcutaneous fat layer; Figure 9 (d) Blood optical parameters; Figure 10 This is a schematic diagram of the biomimetic transmittance experimental device provided by the present invention; wherein, Figure 10 (a) is the experimental setup; Figure 10 (b) is the light source corresponding to a 0° divergence angle; Figure 10 (c) is a light source corresponding to a divergence angle of 60°; Figure 10 (d) represents the light source corresponding to a divergence angle of 120°; Figure 10 (e) is for measuring local light transmittance; Figure 10 (f) represents the measurement area for local light transmittance; Figure 11 This is a schematic diagram of the correlation analysis results provided by the present invention; wherein, Figure 11 (a) is a graph showing the absolute values ​​and correlation analysis of the simulation experiment when the incident angle of the light source is 0°; Figure 11 (b) is a graph showing the absolute values ​​and correlation analysis of the phantom experiment when the incident angle of the light source is 0°; Figure 11 (c) is the light source with a divergence angle of 30° corresponding to the simulation experiment; Figure 11 (d) is the light source with a divergence angle of 30° corresponding to the phantom experiment; Figure 11 (e) is the light source with a divergence angle of 60° corresponding to the simulation experiment; Figure 11 (f) is the light source with a divergence angle of 60° corresponding to the phantom experiment; Figure 12 A schematic diagram of MC simulation results of light transmission in skin at different divergence angles (0º, 30º, 60º, 90º, 120º) provided by the present invention; Figure 13 The light energy deposition distribution map provided by the present invention; wherein, Figure 13 (a) is a distribution map of light energy deposition with the incident light divergence angle at 0º; Figure 13 (b) is a distribution map of light energy deposition with incident light divergence angles of 60º; Figure 13(c) is a distribution map of light energy deposition with incident light divergence angles of 120º; Figure 14 A schematic diagram illustrating the relationship between the divergence angles of incident light and the tissue temperature distribution provided by this invention; wherein, Figure 14 (a) Relationship between temperature along the Z-axis of the model center and the divergence angle of the tissue irradiated with incident light for 1 second; Figure 14 (b) Relationship between temperature along the Z-axis of the model center and the divergence angle of the tissue irradiated with incident light for 600s; Figure 14 (c) At the location with the highest temperature, calculate the temperature change graph over 600 seconds; Figure 14 (d) is a tissue temperature distribution diagram when the divergence angle is 0°; Figure 14 (e) Tissue temperature distribution at a divergence angle of 60°; Figure 14 (f) Tissue temperature distribution at a divergence angle of 120° Figure 15 This is a schematic diagram of energy deposition distribution in tissue provided by the present invention; Figure 16 This is a schematic diagram of the relative depth of light penetration provided by the present invention. Detailed Implementation

[0019] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0020] Example: Please see Figure 1 and Figure 2 This embodiment provides a high-power LED lamp body, including: Immersion gold PCB board 1 is used to provide a circuit conduction path; The vertical structure LED chip 2 has its first connection end fixed to the first circuit conduction path of the immersion gold PCB board 1 using nano-silver paste sintering and die bonding technology. After sintering, the nano-silver paste forms a porous silver powder solder paste layer 3. The second connection end of the LED chip 2 is connected to a gold wire 4, and the other end of the gold wire 4 is connected to the second circuit conduction path of the immersion gold PCB board 1. Several vertical structure LED chips 2 are arranged in a preset arrangement to form a multi-wavelength LED light array. The multi-wavelength LED light array is used to provide a high-power LED light source of a preset wavelength. The preset arrangement includes a rectangular array arrangement, a ring array arrangement, or an interlaced array arrangement, and the arrangement density and area range can be adjusted according to the different usage requirements of the therapeutic device.

[0021] The protective component is connected to the immersion gold PCB board 1 and covers the vertical structure LED chip 2 and gold wire 4.

[0022] Specifically, this invention employs a high-power LED light source, utilizing a vertically structured LED chip 2 and a high thermal conductivity nano-silver paste sintering and die-bonding technology. This technology enables the sintering of porous silver powder solder paste onto the immersion gold PCB board 1. After sintering, the nano-silver paste forms a porous silver powder solder paste layer 3 with a thermal conductivity of up to 240 W / (K·m), while simultaneously preventing oxidation of the vertically structured LED chip 2, thereby improving the LED's heat dissipation performance and stability. Furthermore, to protect the gold wires 4 on the immersion gold PCB board 1 from damage, a method of fixing the frame and glass protective cover with UV-cured adhesive is used. This method prevents damage to the gold wires 4 and improves the overall lifespan and reliability of the device. The structure, spectrum, and light distribution curve of the light source are as follows: Figure 2 As shown, Figure 2 (a) is a model and actual image of a high-power LED lamp body; Figure 2 (b) is the relative spectrum of the LED; Figure 2 (c) shows the LED light distribution curve and three-dimensional light distribution diagram; the maximum output light power of the LED light source can reach 64W.

[0023] In this invention, a porous silver solder paste layer 3 is formed in a high-power LED lamp body used for meridian therapy using nano-silver paste sintering and die-bonding technology. Vertical structure LED chips 2 are directly die-bonded onto an immersion gold PCB substrate. The porous silver solder paste layer 3 forms a high thermal conductivity area, allowing the porous silver solder paste layer 3 to work with the immersion gold PCB board 1 to dissipate heat quickly, improving the overall heat dissipation performance of the high-power LED lamp body, avoiding local heat accumulation, increasing the operating time of the high-power LED lamp body, and extending its service life. Furthermore, several vertical structure LED chips 2 are arranged in a preset layout to form a multi-wavelength LED light array. The multi-wavelength LED light array can provide LED light sources of preset wavelengths, which can meet the therapeutic needs of meridian therapy for different wavelengths of light and improve the adaptability of treatment.

[0024] In this embodiment (not shown in the figure), the protective component includes a frame fixed by UV-curing adhesive and a glass protective cover mounted on the frame. The frame is connected to the immersion gold PCB board 1. The frame and the glass protective cover are used to seal and protect the internal vertical structure LED chip 2 and gold wire 4.

[0025] Specifically, by forming a complete sealed protection for the core structure of the LED light-emitting device through protective components, it can isolate external dust, moisture and impurities from contaminating the chip and gold wire, avoiding short circuits or luminous efficiency decay. At the same time, the UV curing adhesive has a low curing temperature, so the assembly process will not cause thermal damage to the LED chip and die bonding layer. It can also work with the overall structure to maintain the light output efficiency of the lamp body, avoid additional light loss, and ensure that the light power output to the treatment site meets the treatment needs.

[0026] In this embodiment (not shown in the figure), the preset wavelengths are 630nm, 830nm and 940nm.

[0027] Specifically, by using high-power LED light sources of 630nm, 830nm, and 940nm respectively, red light and near-infrared light with different penetration depths can be provided to the skin. These can act on the meridians and surrounding tissues at different depths in the epidermis, dermis, and subcutaneous tissue, matching the treatment needs of different parts and depths of the meridians, and improving the accuracy and effectiveness of meridian treatment.

[0028] In this embodiment (not shown), a composite material heat sink is also included, which is thermally coupled to the gold-plated PCB board 1. The composite material heat sink is combined with active thermal control technology to control the total thermal resistance of the lamp body within a preset range.

[0029] Specifically, to address the heat dissipation issue of high-power light sources, a composite material heat sink design was adopted, combined with active thermal control technology, to ensure that the heat dissipation efficiency of the module does not fall below the preset value during long-term operation. The preset value of heat dissipation efficiency is preferably 85%. Through thermal simulation analysis and multiple test verifications, the total thermal resistance of the light source module was ultimately controlled within a reasonable range. The composite material heat sink includes a graphene thermally conductive layer, an aluminum-based heat sink, and a heat dissipation fin assembly stacked sequentially along the back of the immersion gold PCB board 1. The graphene thermally conductive layer has excellent in-plane thermal conductivity, which can quickly and evenly diffuse the local heat generated by the multiple vertical structure LED chips 2 on the immersion gold PCB board 1, avoiding the accumulation of local hot spots. The aluminum-based heat sink and heat dissipation fin assembly receive the heat and quickly dissipate it to the outside. Combined with the active air cooling structure, the heat exchange is accelerated. Compared with traditional pure aluminum heat sinks, the overall composite material heat sink can reduce the total thermal resistance by more than 15%, ensuring that the chip junction temperature of the high-power LED remains stable within a safe range during long-term operation, avoiding wavelength drift and lifespan decay caused by high temperature, and ensuring that the output light power stably meets the continuous working requirements of meridian therapy.

[0030] Please see Figures 3-6 The present invention provides an LED light source meridian therapy device, including a housing 101: A plurality of high-power LED lamp bodies 102 are installed inside a housing 101, and the plurality of high-power LED lamp bodies 102 are used to provide a high-power LED light source; wherein the wavelength of the LED light source is selected from at least one of 630nm, 810nm or 940nm; An optical system 103 is installed inside a housing 101. The optical system 103 includes an optical integrating rod 1031. A high-power LED lamp body 102 is installed at one end of the optical integrating rod 1031, and an aspherical condenser lens 1032 and a Fresnel lens 1033 are sequentially installed at the other end of the optical integrating rod 1031. The optical integrating rod 1031 is used to homogenize the incident light emitted by the high-power LED lamp body 102. The aspherical condenser lens 1032 is used to initially converge the homogenized light and adjust the divergence angle of the beam. The Fresnel lens 1033 is used to further homogenize and collimate the initially converged beam so that the output light meets the uniformity and spot size requirements for acupoint irradiation. A multi-channel controller 104 is mounted on the housing and is connected to each high-power LED lamp body 102. The multi-channel controller 104 is used to collect and adjust the output parameters of several high-power LED lamp bodies 102 in real time.

[0031] Specifically, the optical system 103 and the multi-channel controller 104 are installed through the housing 101. An aspherical condenser lens 1032 and a Fresnel lens 1033 are sequentially arranged at the other end of the optical integrating rod 1031. The optical integrating rod 1031 fully mixes and homogenizes the light emitted from the light source, transforming the originally unevenly distributed light into a uniform surface light source output. The homogenized light enters the aspherical condenser lens 1032, where the beam divergence angle is reduced by adjusting the aspherical surface shape, achieving initial light convergence and avoiding excessive divergence and energy waste. The initially converged beam then reaches the Fresnel lens 1033, which further homogenizes the beam and adjusts its collimation, ultimately outputting a light spot that meets the requirements for acupoint irradiation, achieving the required uniformity and matching size. The multi-channel controller can independently control the working status of each high-power LED lamp 102, flexibly adjusting the output according to actual treatment needs. The device can adjust the output power of single or multiple lamps, emit light sources of preset wavelengths, and adjust parameters such as emission duration. It also collects the working data of each high-power LED lamp 102 in real time, controlling the peak deviation of the 630nm, 810nm, and 940nm treatment wavelengths within ±3nm to ensure the specificity and effectiveness of photobiological regulation and guarantee the stability and safety of the treatment process. The device has a compact and small overall structure, making it easy to move and operate. It can adapt to the usage needs of different diagnostic and treatment scenarios. The shell is equipped with an external interface for multi-functional expansion, such as connecting to an external control terminal to adjust treatment parameters, read stored work records, or connect to other supporting diagnostic and treatment equipment for combined treatment. The interface also supports power supply, data transmission, and other functions, adapting to the expansion needs of different usage scenarios. It can quickly complete functional upgrades without modifying the main structure of the treatment device, improving the adaptability and service life of the equipment.

[0032] The multi-channel controller 104 includes a signal acquisition module, a control chip, a power adjustment module, and an operation module (not shown) connected in sequence. The signal acquisition module is used to collect the operating current, operating temperature, and actual output light power parameters of each high-power LED lamp in real time. The control chip compares the collected actual parameters with preset parameters and generates corresponding adjustment commands to send to the power adjustment module. The power adjustment module adjusts the input power of each high-power LED lamp accordingly, realizing independent control of a single lamp and meeting the personalized output requirements of different acupoints and treatment scenarios. The operation module has multiple operation buttons and a display screen. Through the operation buttons and the display screen, preset output parameters corresponding to different acupoints can be set, and the actual operating parameters of each high-power LED lamp can be viewed in real time. This makes it convenient for operators to quickly adjust the plan according to treatment needs, and at the same time, it is convenient to detect abnormal equipment status in a timely manner, ensuring the stable operation of the equipment and the safety of the treatment process.

[0033] Furthermore, the Fresnel lens 1033 of the present invention is made of PMMA (polymethyl methacrylate), which has advantages such as low cost and ease of processing. The object-side focal length of the Fresnel lens 1033 is 100mm. The size of the light spot can be controlled by adjusting the distance between the Fresnel lens and the aspherical condenser lens 1032. The overall optical path simulation diagram is shown in Figure 5(a). Figure 5 (b) is the normalized illuminance distribution of the light spot. Figure 5 (c) represents the light distribution intensity at the line position in the illuminance diagram. After the focusing effect of the aspherical condenser lens 1032 and the Fresnel lens 1033, a rectangular light spot with a minimum size of 12mm×12mm and a maximum size of 17mm×17mm can be generated 200mm behind the Fresnel lens 1033, and the collimation of the beam is greatly improved. Figure 6 The optical path of the actual phototherapy device is very close to the optical path simulation results.

[0034] In this embodiment, the aspherical condenser lens 1032 and Fresnel lens 1033 in the optical system 103 control the divergence angle of the light source within 30° to form a stable light dose penetration in biological tissue.

[0035] Specifically, the aspherical condenser lens 1032 and Fresnel lens 1033 can control the divergence angle of the light source within 30°, thereby narrowing the light emission range of the light source and concentrating the energy on the selected acupoint area. This avoids excess light energy spreading to surrounding non-treatment tissues, which not only improves the utilization rate of the light therapy dose at the acupoint location, but also reduces the potential impact of additional irradiation on unrelated tissues, thus better meeting the precise needs of meridian therapy.

[0036] Please see Figure 7 This invention provides a method for constructing a skin optical phantom, the method comprising the following steps: S1: Establish a multi-layer skin optical model. The multi-layer skin optical model includes at least the epidermis, the dermis containing the upper and deep vascular plexuses, and the subcutaneous fat layer. The model is configured with preset thickness, absorption coefficient, and reduced scattering coefficient for each layer. S2: Using agar as a matrix, equipped with absorbents and scattering agents, and based on the optical parameters of the epidermis, dermis and subcutaneous fat layer, respectively, the epidermal phantom and dermal phantom are cast and solidified to form an epidermal phantom and a dermal phantom. S3: The diffuse reflectance and transmittance of the epidermal and dermal phantoms are measured using an integrating sphere system, and the actual absorption coefficient and reduced scattering coefficient of each phantom are calculated based on the inverse Monte Carlo algorithm to ensure that they match the skin optical model. S4: The epidermal phantom and dermal phantom are stacked in anatomical order, and physiological saline is added between the layers to form a multi-layered composite skin optical phantom.

[0037] Specifically, the skin optical phantom construction method proposed in this invention involves establishing a multi-layered optical model that includes at least the epidermis, a dermis containing vascular plexuses, and subcutaneous fat. Each layer of the phantom is then cast and solidified using specific formulations of agar-India ink-fat emulsion or agar-whole pig blood-fat emulsion. The absorption coefficient and reduced scattering coefficient of each layer are then calibrated using an integrating sphere system and an inverse Monte Carlo algorithm. Finally, the layers are superimposed to form a multi-layered composite skin optical phantom. The phantom prepared by this method highly matches the optical parameters of real skin. Furthermore, the correlation between Monte Carlo simulation and phantom experiment transmittance verification ensures the optical equivalence of the phantom. This method also provides a standardized and repeatable physical platform for testing the light penetration dose of LED light source meridian therapy devices. This allows the therapy device to accurately assess tissue penetration depth and energy deposition distribution at different divergence angles and wavelengths during the research and development stage through phantom experiments, thereby optimizing treatment parameters and avoiding the risks and ethical issues of direct human trials.

[0038] In this embodiment, the absorbent is prepared with Indian ink or whole pig blood, and the scattering agent is prepared with fat emulsion; The formulation volume fraction of the epidermal phantom is: 1.5% agar, 0.005% Indian ink and 2% fat emulsion, and the thickness of the epidermal phantom is 1 mm; The dermal phantom consists of an upper dermal phantom and a deep dermal phantom. The upper dermal phantom has a volume fraction of 1.5% agar, 2% fat emulsion, and 1.5% whole pig blood, while the deep dermal phantom has a volume fraction of 1.5% agar, 2% fat emulsion, and 1% whole pig blood. Both the upper and deep dermal phantoms are 2 mm thick.

[0039] In this embodiment, the verification of the multilayer skin optical model and the skin optical phantom was completed through a correlation analysis of transmittance between Monte Carlo simulation and phantom experiments, and the calculated coefficient of determination R... 2 The value is not less than 0.9.

[0040] Specifically, by verifying the multi-layer skin optical model and the skin optical phantom, the optical equivalence between the phantom and real skin is clarified. This enables the LED light source meridian therapy device to complete standardized light penetration dose testing based on the phantom. During the research and development process, the penetration depth and energy deposition data of light in the phantom can be accurately obtained, providing a reliable experimental basis for optimizing and adjusting the treatment parameters of the therapy device.

[0041] The report on the establishment of the skin optical model and the experimental verification of the phantom is as follows: Skin has a highly complex structure that prevents contaminants and microorganisms from penetrating the body and significantly influences incident light. This experiment optically modeled key tissues involved in phototherapy and fabricated an optical phantom of the skin to verify the reliability of the optical model. Since research on LED light sources in the field of light-tissue dose delivery is lacking, Monte Carlo (MC) simulations were used to analyze factors affecting LED light transmission in the skin. Finally, a photothermal effect simulation of the skin was performed to verify the safety of LED photobiological modulation (PBM).

[0042] 1.1 Establishment of Skin Optical Model 1.1.1 Skin Model Structure The skin is divided into several layers according to different optical properties and composition (such as...) Figure 8 The outermost layer of the skin consists of the stratum corneum and the active epidermis, with the stratum corneum providing excellent light shielding. The dermis, located below the epidermis, is composed of connective tissue and cushions the body from stress. To simplify the model, the optical properties of the stratum corneum and the active epidermis are unified. The blood vessel distribution in the dermis is simplified into upper and deep vascular plexuses, which are embedded within the bloodless dermis. The deepest layer in the model is the subcutaneous fat layer, which serves as the background for light transmission.

[0043] Based on the above assumptions, a voxelized skin model was constructed as shown in the figure below, comprising three layers: epidermis, dermis, and subcutaneous fat. Their thicknesses are D1, D2, and D3 (Table 1.1). A thin layer of air was added outside the epidermis to simulate Fresnel reflection occurring in the epidermal layer when therapeutic light is incident. Upper and deep vascular plexuses are embedded in the bloodless dermis. The number of cubic voxels in the skin tissue model is 500×500×400. Each voxel has a size of 0.01×0.01×0.01 mm³. Table 1.1 contains the relevant structural and light source parameters of the skin model. To investigate the effect of the LED light source divergence angle on light penetration, five different incident light divergence angles were defined in the skin model. (0º, 30º, 60º, 90º, 120º). In the program, photon emission is defined as uniform emission in all directions within the divergence angle. By changing the position of the light source, the spot size on the incident surface remains constant. To achieve a stable distribution of photons in the skin tissue, the number of photons is 10⁸.

[0044]

[0045] Table 1.1 Skin model structural parameters and light source parameters 1.1.2 Optical parameters of the skin model Based on the skin characteristics of Asians, Yu Shimojo's team performed sectioning on multiple fresh Japanese human skin tissue samples, separating the epidermis, dermis, and subcutaneous fat samples, and then measuring and analyzing them. Using a dual integrating sphere spectrometer system and inverse Monte Carlo (iMC) technology, they measured the optical properties of each sample, obtaining... Figure 9 The data in this paper covers average tissue optical parameters of the epidermis, dermis, and subcutaneous fat in the range of 400-1000 nanometers. The blue area represents the absorption coefficient. The red area represents the reduced scattering coefficient. Due to individual differences in skin tissue samples, Figure 9 The optical parameters of the tissue may have a large standard deviation. According to... Figure 9 Suitable optical parameters can be found from the fluctuation range. This section uses light with a wavelength of 650 nm in both simulation and experiment. In the LED-PBM process for KOA, 650 nm red light is typically used. Furthermore, the refractive indices of the three skin tissues are set to 1.37, and the refractive index of blood is 1.33. The anisotropy coefficient g of the tissue is assumed to be wavelength-dependent and can be determined by the empirical formula (1.1) derived from a large amount of data. (1.1) The optical properties of blood within blood vessels in a skin model are primarily influenced by two types of hemoglobin: deoxyhemoglobin (Hb) and oxyhemoglobin (HbO2), with extinction coefficients... and Based on experiments by WBGratzer and Kollias, the absorption coefficients of Hb and HbO2 can be calculated using formula (1.2).

[0046] (1.2) in This refers to the extinction coefficients of Hb and HbO2 at different wavelengths. This refers to the concentration of hemoglobin per liter of blood, under normal circumstances. =150 (g / L), 64500 (g / mol) is the molecular weight of hemoglobin. The absorption coefficient calculated from blood is... Figure 9 The graph is shown in (d). Other optical parameters can be obtained based on data provided by the Jacques team.

[0047] 1.1.3 Simulation Parameter Settings In this experiment, we used the MCXLAB program developed by the Fang team to simulate the transmission of light in tissues. MCXLAB is a native MEX version of MCX, compatible with MATLAB and GNU OCTAVE. It compiles the entire MCX code into a single MEX function, which can be directly called in MATLAB or OCTAVE. The input and output files in MCX are replaced by convenient memory structure variables in MCXLAB, making it easier to use and more interactive. The cfg.srctype function is used to set the light source type to "Cone," ensuring that photons are emitted in all directions with equal probability within the divergence angle. The number of photons is set to 10⁸. For the boundary conditions of the model, Fresnel reflections occur at each boundary, and the results have been verified to have high accuracy.

[0048] 1.2 Experimental Study of Skin Phantom At every stage of the development of various optical medical technologies, each key parameter requires calibration and validation. Researchers typically employ tissue phantom experiments to test and optimize the hardware and software of medical devices, as well as various applications. As a standardized testing method, tissue phantoms have been used in many established dosimetry techniques, such as ultrasound, CT, and MRI. These phantoms typically consist of a scattering medium, an absorbing medium, a substrate, and, in some cases, a fluorophore. Some common scattering media include Intralipid, Nutralipid, or Liposyn. These are mostly fat emulsions containing soybean oil, lecithin, and glycerol. Other common scatterers include milk or micron-sized polystyrene spheres. Some of their optical properties can be calculated using Mie scattering theory. Absorbing media include black India Ink or some biological dyes. The substrate is typically deionized water, agar, etc. Researchers develop optical phantoms by mixing the correct proportions of scattering and absorbing media in the substrate, resulting in a suspension with the inherent optical properties required to simulate the tissue. Typical optical properties for human tissue are... Within the range of 0.5-5.0 cm⁻¹, Within the range of 0.2–400 cm⁻¹, the anisotropy factor g ranges from 0.7 to 0.9.

[0049] The most commonly used model by researchers is the liquid tissue phantom, which uses an aqueous solution of a fat emulsion such as Intralipid as the scattering medium and a water-soluble dye such as India Ink as the absorption medium. However, its key limitation is the difficulty in reproducing non-uniform structures. Firbank proposed using a synthetic model made of resin. A suspension of organic dyes and titanium dioxide particles is added to the resin matrix. Once cured, the resin can be processed into a solid non-uniform phantom with controllable optical properties. The main limitation of this method is the complexity of the preparation process, which makes it difficult to easily change the optical properties and geometry of the model according to the usual requirements of the research stage. Therefore, our method incorporates Intralipid and India Ink solutions into a liquid solution by adding agar. The reason for using agar as the substrate is that it gives the sample higher hardness and toughness compared to liquid phantoms. In addition, high-purity agar powder has almost no absorption and very low turbidity.

[0050] A qualified tissue phantom should meet the following requirements: (1) it should simulate the geometric and optical parameters of physiological structures related to light transmission; (2) all components must be compatible with each other in terms of chemical stability and spectral properties; (3) the relevant parameters of radiative transmission must be predictable and reproducible from the sample composition; (4) the physical parameters of the phantom sample should be stable over time (evaporation, diffusion, aging) and independent of environmental influences; (5) the phantom should allow the construction of non-uniform samples by stacking phantom plates or by fabrication molding techniques; and (6) sample preparation should be simple, fast and safe.

[0051] 1.2.1 Experimental Principles and Preparation Process of Phantoms Because the thickness of the fat layer varies in different areas and its impact on light transmission is relatively small, only the epidermis and the upper and lower dermal layers were considered in the phantom experiments, corresponding to the two types of dermal layers containing upper and lower vascular plexuses in the skin model. The skin phantom used agar (V900510, Sigma, USA) as the matrix, India Ink (4001, Pelikan, GER) and whole porcine blood (B1612, Bersee, CHN) as absorbents, and Intralipid fat emulsion (20%, SSPC, CHN) as a scattering agent. The fabrication process is as follows: (1) Use two rectangular acrylic plates to clamp a U-shaped acrylic plate to form an acrylic mold. Fix it around the mold with clamps. Make skin tissue phantoms of different thicknesses by changing the thickness of the U-shaped acrylic plate in the middle. (2) Dissolve agarose in distilled water using a microwave oven and boil it. After cooling to 60°C, add 20% Intralipid solution as the tissue phantom substrate material. Place it in a water bath at 60°C for 30 minutes, stirring constantly to ensure the medium is fully homogeneous. (3) Take a portion of the base solution, add India Ink solution, and inject it into a 1mm thick epidermal layer mold using a syringe. Place the mold in a refrigerator to cool. Take two more portions of the base solution, add different amounts of whole pig blood to each, and place them into two 2mm thick dermal layer molds to create upper and lower dermal layer phantoms.

[0052] The volume fractions of each reagent are listed in Table 1.2. After cooling and demolding, optical properties were measured. The results showed that the established skin phantom could well simulate the situation after light penetrates to the dermis. Since the thickness of the phantom differs from that of real skin, this experiment adjusted the optical properties of the phantom by changing the concentrations of absorbers and scatterers in the phantom to improve its optical correlation with real skin. After measuring the optical properties of the three-layer phantom, the three phantoms were stacked. To prevent air bubbles from forming in the middle, an appropriate amount of physiological saline was added to the contact surfaces of each layer for buffering.

[0053]

[0054] Table 1.2 Recipes required for making prosthetic bodies (no data indicates no additions) 1.2.2 Measurement of phantom optical parameters The IAD method provides a tool for quickly and accurately solving inverse scattering problems. It is based on the general method proposed by van for solving the planar parallel layer transport equation and introduced into tissue optics by Prahl. A significant advantage of applying the IAD method to tissue optics is that iterative solutions can be obtained quickly using state-of-the-art microcomputers; furthermore, it is flexible enough to consider the anisotropy of scattering and internal reflections at sample boundaries. The method includes the following steps: (1) selection of the optical parameters to be measured; (2) calculation of reflection and transmission; (3) comparison of the calculated and measured reflectance and transmittance; (4) repeating the procedure until the estimated and measured values ​​meet the required accuracy.

[0055] Using a single integrating sphere system, the commonly used therapeutic light wavelength of 650nm was tested (OBIS, Coherent, USA). When measuring the diffuse reflectance of the tissue phantom, a reflectance standard is required; typically, a high-reflectance standard plate with a magnesium oxide or barium sulfate coating is selected. During reflectance measurement, the signal intensity detected by the detector in the three cases shown in the image above is recorded, and the diffuse reflectance MR of the tissue phantom is calculated using the following formula: (1.3) The same method applies to transmission; the measured total transmittance MT is defined as: (1.4) The optical properties of the tissue were then calculated using the IAD algorithm, assuming the scattering anisotropy factor g of the phantom to be 0.7 and the refractive index to be 1.37. The parameters used in the IAD algorithm are listed in Table 1.3.

[0056]

[0057] Table 1.3 Parameters required for the IAD algorithm The results of the tissue phantom optical properties measured using a single integrating sphere system are listed in Table 1.4. According to the final calculation results, although the epidermis, superficial dermis, and deep dermis used the same volume fraction of Intralipid, the reduced scattering coefficient of India Ink was larger due to the scattering of light by ink molecules, while the reduced scattering coefficient caused by whole blood had a relatively smaller impact.

[0058]

[0059] Table 1.4 Phantom optical parameters calculated by the IAD algorithm 1.3 Results of Monte Carlo Simulation and Phantom Experiments 1.3.1 Correlation Results between Simulation and Phantom Experiments By comparing the transmittance trends of the tissue phantom under different incident scattering angles of the light source and correlating them with the MC simulation results, the accuracy of the skin model in Section 1.1 can be verified. This experiment tested the penetration capability of the LED light source in the skin phantom at different scattering angles. The device mainly consists of a light source (LumiEngin, Keyi-Sky, CHN), a collimating lens (ACL5040U, Thorlabs, USA), an aperture (ID36, Thorlabs, USA), an integrating sphere (AIS-2-0.5m, EverFine, CHN), and a spectrometer (HAAS-1200, EverFine, CHN).

[0060] Fix the skin model at the light inlet of the integrating sphere (see...) Figure 10 (a) Then, an LED light source with a center wavelength of 650 nm was selected, the divergence angle was adjusted using a collimating lens, and the diameter of the incident surface was kept consistent by changing the distance between the light source and the sample. Figure 10 (b)-(d) show schematic diagrams of the light source at three divergence angles (0º, 60º, 120º). Optical power data were collected using an integrating sphere and a spectrometer. The average light transmittance obtained from the phantom experiment can be calculated according to formula (1.5). : (1.5) P1 represents the optical power of the LED light source after passing through the unloaded fixture, and P2 represents its optical power after passing through the skin phantom. In addition to measuring the average transmittance, an optical power meter (PM100D, Thorlabs, USA, S120VC probe) was used to measure... Figure 10 (f) shows the optical power in nine regions before and after incident on the skin phantom. The optical power meter probe is placed... Figure 10 (e) The bottom of the fixture. Local transmittance can also be calculated according to formula (1.5).

[0061] For phantom experiments, the MC model calculated... Figure 10 Transmittance within the region is defined as .

[0062] (1.6) In MC simulation, and These represent the luminous flux in the incident and emitted regions, respectively. The sampling area for local transmittance is 1 mm × 1 mm. If the skin corresponding to different regions in the three divergence angle experiments... and If there is a good correlation between them, the skin model can be considered accurate.

[0063] Based on formulas (1.5) and (1.6), the effects of light sources with different divergence angles were analyzed. and . Figure 11 Described and The absolute value difference, such as Figure 11 (a)(c)(e); differences in correlation, such as Figure 11 (b)(d)(f).

[0064] from Figure 11 The following conclusions can be drawn from this: (1) Although and While the absolute values ​​differ somewhat, the trend is consistent. Calculations show that the R² values ​​are all above 0.9. Therefore, and It has a high correlation and can verify the accuracy of the skin model.

[0065] (2) The absolute deviation between the simulated and experimental values ​​is caused by a variety of factors. First, the content of absorbers and scatterers in the phantom is highly correlated with the transmittance of light in the experiment. Changing the composition of the phantom and increasing the content of absorbers and scatterers in the phantom will reduce the transmittance in the experiment. In addition, it has been reported that the size of the light spot is positively correlated with the light penetration ability. Therefore, using a larger light spot size in the phantom experiment may also be one of the reasons for the higher transmittance.

[0066] (3) The divergence angle has a significant impact on the optical transmittance. As the divergence angle increases, the photon path length and backscattering also increase, which leads to a decrease in light penetration ability, such as... Figure 11 (a)(c)(e).

[0067] (4) When the PBM area is large, the transmittance of different areas is different. This is related to the distance from the PBM treatment center, and the transmittance is higher in the part closer to the center.

[0068] (5) When light passes through the epidermis and dermis of the skin, it is significantly attenuated. Therefore, the skin can be considered the most critical part affecting light transmission during PBM treatment.

[0069] 1.3.2 Relationship between LED therapeutic light penetration and light source divergence angle Since the target tissue is often located subcutaneously during phototherapy, excessive photon energy deposition in the skin can lead to insufficient light dose at the target tissue. Compared to lasers, LEDs have a divergence angle issue. Therefore, this experiment investigated the effect of the light source divergence angle on photon transmission in the skin. A simulation method was used, selecting the normalized energy deposition along the Z-axis at the center of the skin model. Conduct a simulation.

[0070] This experiment used light sources with different divergence angles and a wavelength of 650 nm in the simulation. For example... Figure 12 The results showed three distinct elevations, representing the influence of blood vessels in the epidermis, subepithelial region, and deep dermis, respectively. At a divergence angle of 0°, The value is 45% of the value when the incident angle is 60°. As the divergence angle increases, The value also increases accordingly. One reason for this is that the larger the divergence angle, the worse the uniformity of light irradiation on the surface, resulting in a high energy density at the center and a low density around the periphery. Furthermore, the divergence angle increases the path of photons in the tissue and enhances backscattering. When the divergence angle is below 30°, it leads to a decrease in energy deposition in the skin. Based on the above analysis, we can conclude that controlling the beam at a smaller angle is beneficial to improving the light's penetration ability in the tissue. Because the divergence angle of the light source increases, the path of photons in the tissue and the ability to backscatter are enhanced, leading to increased surface energy deposition, while the energy received by deeper tissues decreases. To ensure that deeper tissues receive a sufficient light dose while avoiding damage to surface tissues, the phototherapy time or light source power can be appropriately increased.

[0071] from Figure 12 Analysis showed that incident light with a larger divergence angle deposited more energy along the z-axis at the center position than incident light with a smaller divergence angle. To better understand the distribution of therapeutic light with different divergence angles in tissue, a common wavelength of 650 nm was selected to study the cross-sectional distribution of light at three incident angles (0°, 60°, 120°). Figure 13 As can be seen in (a)-(c), the energy at the center increases continuously with the increase of the angle, but the range of energy deposition decreases continuously, and the light energy on both sides decreases. This is due to Fresnel reflection and the backscattering of photons caused by large-angle oblique incidence, which causes them to leave the tissue.

[0072] 1.3.3 Tissue photothermal analysis After absorbing photon energy, skin tissue will inevitably experience a temperature change. Since the temperature changes caused by different LED divergence angles have not yet been studied, a large temperature change due to this factor may pose a risk of tissue thermal damage. Therefore, it is necessary to analyze the heat distribution of tissue under irradiation at different LED divergence angles. We use the following Pennes biothermal equation to describe the temperature T change of a biological system under the influence of a heat source: The meanings of the parameters in the formula are explained in Table 1.5. In the photothermal simulation used in this experiment, the effect of blood flow in tissues is simulated through blood perfusion. The formula represents the energy deposition generated after light incident on the tissue. As a heat source, According to Figure 13 The results were obtained. The paper ignores skin evaporation and sets the ambient temperature to 37 degrees Celsius, then performs a weighted average of the thermal properties of the three tissues in the skin to obtain a homogenized tissue thermal model. We utilized the kWaveDiffusion function from the K-wave software package for the tissue thermal analysis.

[0073]

[0074] Will Figure 13 The 3D data Q of the photoelectric energy deposition was input into the Pennes biothermal equation for calculation. Figure 14 (a) and (b) show the temperature distribution along the central Z-axis after 1 second and 600 seconds, respectively, at different divergence angles. It can be seen that the light distribution initially increases and then decreases to a stable value. Based on this curve distribution, it can be considered that the location with the largest temperature change caused by phototherapy is located inside the tissue. This location was extracted, and the temperature change curve over time at this location was plotted. Figure 14 (c) Figure. Since the temperature changes significantly in the initial stage and then plateaus, the temperature measurement process was divided into two stages: the first stage was 0-20 seconds with a step size of 0.5 seconds, and the second stage was 20 to 600 seconds with a step size of 20 seconds. The temperature changes during irradiation at different divergence angles were compared. It can be clearly seen that the divergence angle of the therapeutic light has a significant impact on the temperature of the skin epidermis; a light source of the same power can produce a temperature difference of 3°C in the epidermal layer. Figure 14 The difference between the temperature distribution and energy deposition distribution is observed at 650 nm for (d)-(f). It can be seen that the diffusion of temperature makes the values ​​between individual voxels tend to be smooth, and the influence at the vascular plexus is also weakened. However, the area with larger energy deposition due to the divergence angle also produces a corresponding high temperature.

[0075] Although the divergence angle of LED light causes some local temperature differences, in reality, due to the influence of heat dissipation from the skin surface, as long as the incident power is controlled within a safe range, the risk of thermal damage caused by the angle is small.

[0076] 1.3.4 Relationship between LED therapeutic light penetration and light source wavelength Following the previous two sections' investigation of the effects of the therapeutic light source divergence angle on the light dose and photothermal effect in tissue, this section will further investigate the effect of wavelength on the light dose. We selected light rays with wavelengths of 650 nm, 820 nm, and 940 nm, commonly found in LED-PBMs, and applied them along the Z-axis in a skin model. The value is used as the analysis standard. The light source is incident perpendicularly on the skin surface, and the influence of the divergence angle on the light dose is controlled. Figure 9 This demonstrates the corresponding skin and blood optical parameters for these wavelengths. The research results are as follows: Figure 15 As shown, with increasing wavelength, the epidermal layer... The energy density gradually decreases, allowing more energy to penetrate deeper into the skin. At a 0° divergence angle, the normalized energy density of the epidermal layer from an 820 nm wavelength light source is 39.5% of that from a 650 nm wavelength, and the normalized energy density from a 940 nm wavelength is 52.5% of that from an 820 nm wavelength. This is likely due to the reduced melanin absorption and scattering coefficients at 820 and 940 nm wavelengths. The differences in values ​​are not so significant. The effect of wavelength on energy density aligns with the recently published World Association for Laser Therapy (WALT) guidelines. WALT states that the light dose at 904 nm is half that of 780-820 nm. Comparing the energy density of epithelial and deep dermal blood vessels, the values ​​from 820 nm and 940 nm wavelength sources are very close. In contrast, the 650 nm wavelength source only produces the energy density of the other two wavelengths. The value was 37.8%. Higher energy uptake in both vascular plexuses can promote blood circulation, which may also play a positive role in KOA treatment. Therefore, we need to consider not only the effects of different wavelengths of light on photochemical reactions, but also the light dose.

[0077] 1.3.5 Overall Organizational Analysis In general, the changes in transmittance due to the divergence angle of the light source and the changes due to wavelength are both significant. To better understand the effect of divergence angle on the transmission of light of different wavelengths in tissue, the maximum depth at which the transmittance of LED light at different angles is 1 / e within the range of 400nm-1000nm was statistically analyzed. Figure 16 As shown, it can be clearly seen that as the wavelength of light increases, the penetration depth also gradually increases, but the growth trend gradually slows down. This is mainly related to the fact that water in the tissue has a greater absorption of long-wavelength light. Figure 16 It can provide guidance for different light sources. Researchers and medical professionals can use this information to adjust the dosage when evaluating diagnostic and therapeutic applications. When the LED light source has a large divergence half-angle, the dosage needs to be increased to ensure that the target surface receives a sufficient dose.

[0078] The above description is only a preferred embodiment of the present invention, but the scope of protection of the present invention is not limited thereto. Any equivalent substitutions or modifications made by those skilled in the art within the scope of the technology disclosed in the present invention, based on the technical solution and inventive concept of the present invention, should be covered within the scope of protection of the present invention.

Claims

1. A high-power LED lamp body, characterized in that, include: Immersion gold PCB board, wherein the immersion gold PCB board is used to provide circuit conduction path; A vertical structure LED chip, wherein the first connection end of the vertical structure LED chip is fixed to the first circuit conduction path of the immersion gold PCB board by nano silver paste sintering and die bonding technology, the nano silver paste forms a porous silver powder solder paste layer after sintering, the second connection end of the LED chip is connected to gold wire, and the other end of the gold wire is connected to the second circuit conduction path of the immersion gold PCB board. A plurality of the vertical structure LED chips are arranged in a preset arrangement to form a multi-wavelength LED light array, the multi-wavelength LED light array is used to provide a high-power LED light source of a preset wavelength; A protective component is connected to an immersion gold PCB board and covers the vertical structure LED chip and gold wire.

2. The high-power LED lamp body according to claim 1, characterized in that, The protective assembly includes a frame fixed by UV-curing adhesive and a glass protective cover mounted on the frame. The frame is connected to an immersion gold PCB board. The frame and the glass protective cover are used to seal and protect the internal vertical structure LED chips and gold wires.

3. The high-power LED lamp body according to claim 2, characterized in that, The preset wavelengths are 630nm, 830nm, and 940nm.

4. The high-power LED lamp body according to claim 3, characterized in that, It also includes a composite material heat sink that is thermally coupled to the immersion gold PCB board. The composite material heat sink incorporates active thermal control technology to control the total thermal resistance of the lamp body within a preset range.

5. An LED light source meridian therapy device, employing a high-power LED lamp body as described in any one of claims 1-4, characterized in that, Includes the housing: A plurality of high-power LED lamp bodies are installed inside a housing, and the plurality of high-power LED lamp bodies are used to provide a high-power LED light source; An optical system is installed inside a housing. The optical system includes an optical integrating rod, one end of which is equipped with a high-power LED lamp body, and the other end of which is sequentially equipped with an aspherical condenser lens and a Fresnel lens. A multi-channel controller is mounted on the housing and is connected to each high-power LED lamp body. The multi-channel controller is used to collect and adjust the output parameters of several high-power LED lamp bodies in real time.

6. The LED light source meridian therapy device according to claim 5, characterized in that, The aspherical condenser lens and Fresnel lens in the optical system control the divergence angle of the light source within 30° to achieve stable light dose penetration in biological tissues.

7. The LED light source meridian therapy device according to claim 6, characterized in that, The wavelength of the LED light source is selected from at least one of 630nm, 810nm, or 940nm.

8. A method for constructing a skin optical phantom, used to verify the optical penetration performance of an LED light source meridian therapy device as described in any one of claims 5-7, characterized in that, The method includes the following steps: S1: Establish a multi-layer skin optical model, which includes at least the epidermis, the dermis containing the upper vascular plexus and the deep vascular plexus, and the subcutaneous fat layer, and configure preset thickness, absorption coefficient and reduced scattering coefficient for each layer. S2: Using agar as a matrix, equipped with absorbents and scattering agents, and based on the optical parameters of the epidermis, dermis and subcutaneous fat layer, respectively, an epidermal phantom and a dermal phantom are cast and solidified to form an epidermal phantom and a dermal phantom. S3: Use an integrating sphere system to measure the diffuse reflectance and transmittance of the epidermal and dermal phantoms, and calculate the actual absorption coefficient and reduced scattering coefficient of each phantom layer based on the inverse Monte Carlo algorithm to ensure that they match the skin optical model. S4: The epidermal phantom and the dermal phantom are stacked in anatomical order, and physiological saline is added between the layers to form a multi-layered composite skin optical phantom.

9. The method for constructing a skin optical phantom according to claim 8, characterized in that, The absorbent is formulated with Indian ink or whole pig blood, and the scattering agent is formulated with a fat emulsion; The formulation volume fraction of the epidermal phantom is: 1.5% agar, 0.005% Indian ink and 2% fat emulsion, and the thickness of the epidermal phantom is 1 mm; The dermal phantom comprises an upper dermal phantom and a deep dermal phantom. The upper dermal phantom has a volume fraction of 1.5% agar, 2% fat emulsion, and 1.5% whole pig blood. The deep dermal phantom has a volume fraction of 1.5% agar, 2% fat emulsion, and 1% whole pig blood. The thickness of both the upper and deep dermal phantoms is 2 mm.

10. The method for constructing a skin optical phantom according to claim 9, characterized in that, The verification of the multilayer skin optical model and skin optical phantom was completed through Monte Carlo simulation and phantom experiment transmittance correlation analysis, and the calculated coefficient of determination R... 2 The value is not less than 0.9.

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